Vessel sealing instrument

ABSTRACT

A bipolar electrosurgical instrument for clamping, grasping, manipulating, and sealing tissue includes first and second shafts each having a jaw member extending from a distal end thereof and a handle disposed at a proximal end thereof. The handle being operable to effect movement of the jaw members relative to one another from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members cooperate to grasp tissue therebetween. The bipolar instrument is connectable to a source of electrical energy having a first electrical potential connected to one of the jaw members and a second electrical potential connected to the other of the jaw members such that the jaw members are capable of selectively conducting energy through tissue held therebetween to effect a seal. Both the first and second electrical potentials are transmitted to the jaw members through the first shaft.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part of PCT Application Serial No. PCT/US01/11420 filed on Apr. 6, 2001 which is a continuation-in-part of U.S. application Ser. No. 09/425,696 filed Oct. 22, 1999 by Philip Mark Tetzlaff et al. which is a continuation-in-part of U.S. application Ser. No. 09/178,027 filed Oct. 23, 1998 by Philip Mark Tetzlaff et al., the entire contents of each of these applications are hereby incorporated by reference.

BACKGROUND

The present disclosure relates to forceps used for open surgical procedures. More particularly, the present disclosure relates to a forceps which applies a combination of mechanical clamping pressure and electrosurgical current to seal tissue.

TECHNICAL FIELD

A hemostat or forceps is a simple plier-like tool which uses mechanical action between its jaws to constrict vessels and is commonly used in open surgical procedures to grasp, dissect and/or clamp tissue. Electrosurgical forceps utilize both mechanical clamping action and electrical energy to effect hemostasis by heating the tissue and blood vessels to coagulate, cauterize and/or seal tissue.

Certain surgical procedures require sealing and cutting blood vessels or vascular tissue. Several journal articles have disclosed methods for sealing small blood vessels using electrosurgery. An article entitled Studies on Coagulation and the Development of an Automatic Computerized Bipolar Coagulator, J. Neurosurg., Volume 75, July 1991, describes a bipolar coagulator which is used to seal small blood vessels. The article states that it is not possible to safely coagulate arteries with a diameter larger than 2 to 2.5 mm. A second article is entitled Automatically Controlled Bipolar Electrocoagulation—“COA-COMP”, Neurosurg. Rev. (1984), pp. 187-190, describes a method for terminating electrosurgical power to the vessel so that charring of the vessel walls can be avoided.

By utilizing an electrosurgical forceps, a surgeon can either cauterize, coagulate/desiccate, reduce or slow bleeding and/or seal vessels by controlling the intensity, frequency and duration of the electrosurgical energy applied to the tissue. Generally, the electrical configuration of electrosurgical forceps can be categorized in two classifications: 1) monopolar electrosurgical forceps; and 2) bipolar electrosurgical forceps.

Monopolar forceps utilize one active electrode associated with the clamping end effector and a remote patient return electrode or pad which is typically attached externally to the patient. When the electrosurgical energy is applied, the energy travels from the active electrode, to the surgical site, through the patient and to the return electrode.

Bipolar electrosurgical forceps utilize two generally opposing electrodes which are disposed on the inner opposing surfaces of the end effectors and which are both electrically coupled to an electrosurgical generator. Each electrode is charged to a different electric potential. Since tissue is a conductor of electrical energy, when the effectors are utilized to grasp tissue therebetween, the electrical energy can be selectively transferred through the tissue.

In order to effect a proper seal with larger vessels, two predominant mechanical parameters must be accurately controlled—the pressure applied to the vessel and the gap between the electrodes both of which affect thickness of the sealed vessel. More particularly, accurate application of the pressure is important to oppose the walls of the vessel, to reduce the tissue impedance to a low enough value that allows enough electrosurgical energy through the tissue, to overcome the forces of expansion during tissue heating and to contribute to the end tissue thickness which is an indication of a good seal. It has been determined that a fused vessel wall is optimum between 0.001 and 0.005 inches. Below this range, the seal may shred or tear and above this range the lumens may not be properly or effectively sealed.

With respect to smaller vessel, the pressure applied to the tissue tends to become less relevant whereas the gap distance between the electrically conductive surfaces becomes more significant for effective sealing. In other words, the chances of the two electrically conductive surfaces touching during activation increases as the vessels become smaller.

Electrosurgical methods may be able to seal larger vessels using an appropriate electrosurgical power curve, coupled with an instrument capable of applying a large closure force to the vessel walls. It is thought that the process of coagulating small vessels is fundamentally different than electrosurgical vessel sealing. For the purposes herein, “coagulation” is defined as a process of desiccating tissue wherein the tissue cells are ruptured and dried and vessel sealing is defined as the process of liquefying the collagen in the tissue so that it reforms into a fused mass. Thus, coagulation of small vessels is sufficient to permanently close them. Larger vessels need to be sealed to assure permanent closure.

Numerous bipolar electrosurgical forceps have been proposed in the past for various open surgical procedures. However, some of these designs may not provide uniformly reproducible pressure to the blood vessel and may result in an ineffective or non-uniform seal. For example, U.S. Pat. No. 2,176,479 to Willis, U.S. Pat. Nos. 4,005,714 and 4,031,898 to Hiltebrandt, U.S. Pat. Nos. 5,827,274, 5,290,287 and 5,312,433 to Boebel et al., U.S. Pat. Nos. 4,370,980, 4,552,143, 5,026,370 and 5,116,332 to Lottick, U.S. Pat. No. 5,443,463 to Stern et al., U.S. Pat. No. 5,484,436 to Eggers et al. and U.S. Pat. No. 5,951,549 to Richardson et al., all relate to electrosurgical instruments for coagulating, cutting and/or sealing vessels or tissue.

Many of these instruments include blade members or shearing members which simply cut tissue in a mechanical and/or electromechanical manner and are relatively ineffective for vessel sealing purposes. Other instruments rely on clamping pressure alone to procure proper sealing thickness and are not designed to take into account gap tolerances and/or parallelism and flatness requirements which are parameters which, if properly controlled, can assure a consistent and effective tissue seal. For example, it is known that it is difficult to adequately control thickness of the resulting sealed tissue by controlling clamping pressure alone for either of two reasons: 1) if too much force is applied, there is a possibility that the two poles will touch and energy will not be transferred through the tissue resulting in an ineffective seal; or 2) if too low a force is applied, a thicker less reliable seal is created.

As mentioned above, in order to properly and effectively seal larger vessels, a greater closure force between opposing jaw members is required. It is known that a large closure force between the jaws typically requires a large moment about the pivot for each jaw. This presents a challenge because the jaw members are typically affixed with pins which are positioned to have a small moment arms with respect to the pivot of each jaw member. A large force, coupled with a small moment arm, is undesirable because the large forces may shear the pins. As a result, designers must compensate for these large closure forces by either designing instruments with metal pins and/or by designing instruments which at least partially offload these closure forces to reduce the chances of mechanical failure. As can be appreciated, if metal pivot pins are employed, the metal pins must be insulated to avoid the pin acting as an alternate current path between the jaw members which may prove detrimental to effective sealing.

Increasing the closure forces between electrodes may have other undesirable effects, e.g., it may cause the opposing electrodes to come into close contact with one another which may result in a short circuit and a small closure force may cause pre-mature movement of the issue during compression and prior to activation.

Thus, a need exists to develop a bipolar forceps which effectively seals vascular tissue and solves the aforementioned problems by providing an instrument which enables a large closure force between the opposing jaws members, reduces the chances of short circuiting the opposing jaws during activation and assists in manipulating, gripping and holding the tissue prior to and during activation.

SUMMARY

The present disclosure relates to a bipolar electrosurgical instrument for use in open surgery which includes first and second shafts one of which is connectable to a source of electrosurgical energy. Each shaft includes a jaw member extending from a distal end thereof and a handle disposed at a proximal end thereof for effecting movement of the jaw members relative to one another from a first, open position wherein the jaw members are disposed in spaced relation relative to one another to a second, closed position wherein the jaw members cooperate to grasp tissue therebetween. The source of electrical energy effects first and second electrical potentials in the respective jaw members such that the jaw members are capable of selectively conducting energy through tissue held therebetween to effect a seal.

Preferably, the first and second electrical potentials are created at the jaw members through the first shaft. For example, in one embodiment, the first electrical potential is transmitted through the first shaft by a lead having a terminal end which electrically interfaces with a distal connector which connects a first jaw member to the first electrical potential. The second electrical potential is transmitted through the first shaft by a tube disposed within the first shaft which connects the second jaw member to the second electrical potential.

The first and second jaw members are connected about a pivot pin. The distal connector is preferably interposed between the jaw members and includes a series of flanges which are dimensioned to prevent the emanation of stray currents from the electrically conductive sealing surfaces of the jaw members during activation.

Preferably, the distal connector includes a spring washer or wave washer which acts as an electrical intermediary between the terminal end and the jaw member. In one embodiment, the spring washer is beveled to enhance the electrical interface between the terminal end and the jaw member, i.e., beveling causes the spring washer to rotate relative the terminal end during movement of the jaw members from the first to second positions which provides a self-cleaning, enhanced running electrical contact between the terminal end and the jaw member.

Preferably, the distal connector is made from an insulative substrate and is disposed between the jaw members for electrically isolating the first and second potentials. In one embodiment, the distal connector includes a first surface having at least one recess defined therein which is dimensioned to receive at least a portion of the terminal end of the lead.

In yet another embodiment, one of the jaw members includes a skirt which is dimensioned to prevent exposure of the terminal end during all angles of operation, i.e., when the jaw members are disposed in the first position, the second position and/or during operative movement therebetween.

The lead preferably includes a inner core made from a solid or multi-strand electrically conductive material, e.g., copper/aluminum wire, which is surrounded by an insulative, non-conductive coating, e.g., plastic. In one embodiment, the terminal or distal end of the electrically conductive material is flattened, i.e., “flat-formed”, and is dimensioned to substantially encircle a boss which extends from the surface of the distal connector. Preferably, the boss is designed to electrically insulate the terminal end of the lead from the pivot pin.

In another embodiment, at least one non-conductive stop member is disposed on an electrically conductive sealing surface of one of the jaw members. The stop members are designed to control/regulate the distance, i.e., gap, between the jaw members when tissue is held therebetween during activation.

BRIEF DESCRIPTION OF THE DRAWINGS

Various embodiments of the subject instrument are described herein with reference to the drawings wherein:

FIG. 1 is a left, perspective view of a forceps according to the present disclosure;

FIG. 2 is an enlarged, perspective view of an end effector assembly of the forceps of FIG. 1 shown in open configuration;

FIG. 2′ is an enlarged view of the distal end of a bipolar instrument incorporated by reference from a prior disclosure;

FIG. 3 is an enlarged, perspective view of the end effector assembly of the forceps of FIG. 1 shown in closed configuration;

FIG. 4A is an exploded view of the forceps according to the present disclosure;

FIG. 4B is an enlarged, exploded view of the end effector assembly of FIG. 4A showing the electrical connection of a distal electrical connector for supplying electrical energy to the end effector assembly;

FIG. 4′ is an enlarged, exploded view of the end effector assembly of a bipolar instrument incorporated by reference from a prior disclosure;

FIG. 5 is an enlarged, top perspective view of a lower jaw member of forceps with the distal connector seated thereon;

FIG. 5′ is an enlarged view of a distal end of a bipolar instrument incorporated by reference from a prior disclosure;

FIG. 6 is a right, perspective view of the forceps of FIG. 1 shown grasping a tissue structure;

FIG. 6A′-6G′ are enlarged views of jaw members and stop configurations of a bipolar instrument incorporated by reference from a prior disclosure;

FIG. 7 is a enlarged view of the indicated area of detail in FIG. 4A showing a proximal electrical interface/connector for supplying electrical energy to the end effector assembly; and

FIG. 8 is a cross section of the forceps of FIG. 6 showing the electrical feed path of a first lead having a first electrical potential and showing the electrical connection of the proximal electrical interface of FIG. 7 with a second lead having a second electrical potential.

DETAILED DESCRIPTION

Referring now to FIGS. 1-4, a forceps 10 for use with open surgical procedures includes elongated shaft portions 12 a and 12 b each having a proximal end 16 a and 16 b, respectively, and a distal end 14 a and 14 b, respectively. In the drawings and in the descriptions which follow, the term “proximal”, as is traditional, will refer to the end of the forceps 10 which is closer to the user, while the term “distal” will refer to the end which is further from the user.

The forceps 10 includes an end effector assembly 100 which attaches to distal ends 14 a and 14 b of shafts 12 a and 12 b, respectively. As explained in more detail below, the end effector assembly 100 includes pair of opposing jaw members 110 and 120 which are pivotably connected about a pivot pin 150.

Preferably, each shaft 12 a and 12 b includes a handle 17 a and 17 b disposed at the proximal end 16 a and 16 b thereof which each define a finger hole 18 a and 18 b, respectively, therethrough for receiving a finger of the user. As can be appreciated, finger holes 18 a and 18 b facilitate movement of the shafts 12 a and 12 b relative to one another which, in turn, pivot the jaw members 110 and 120 from an open position (FIG. 2) wherein the jaw members 110 and 120 are disposed in spaced relation relative to one another to a clamping or closed position (FIG. 3) wherein the jaw members 110 and 120 cooperate to grasp tissue 400 (FIG. 6) therebetween.

A ratchet 30 is preferably included for selectively locking the jaw members 110 and 120 relative to one another at various positions during pivoting. As best shown in FIG. 6, a first ratchet interface, e.g., 30 a, extends from the proximal end 16 a of shaft member 12 a towards a second ratchet interface 30 b in a generally vertically aligned manner such that the inner facing surfaces of each ratchet 30 a and 30 b abut one another upon closure about the tissue 400. Preferably, each ratchet interface 30 a and 30 b includes a plurality of flanges 32 a and 32 b, respectively, which projects from the inner facing surface of each ratchet interface 30 a and 30 b such that the ratchet interfaces 30 a and 30 b interlock in at least one position. In the embodiment shown in FIG. 6, the ratchet interfaces 30 a and 30 b interlock at several different positions.

Preferably, each position associated with the cooperating ratchet interfaces 30 a and 30 b holds a specific, i.e., constant, strain energy in the shaft members 12 a and 12 b which, in turn, transmits a specific closing force to the jaw members 110 and 120. It is envisioned that the ratchet 30 may include graduations or other visual markings which enable the user to easily and quickly ascertain and control the amount of closure force desired between the jaw members. A design without a ratchet system or similar system would require the user to hold the jaw members 110 and 120 together by applying constant force to the handles 17 a and 17 b which may yield inconsistent results.

As best illustrated in FIG. 1, one of the shafts, e.g., 12 b, includes a proximal shaft connector 19 which is designed to connect the forceps 10 to a source of electrosurgical energy such as an electrosurgical generator (not shown). More particularly, proximal shaft connector 19 is formed by a cover 19 a and a flange 19 b which extends proximally from shaft 12 b. Preferably, cover 19 a and flange 19 b mechanically cooperate to secure an electrosurgical cable 210 to the forceps 10 such that the user may selectively apply electrosurgical energy as needed.

The proximal end of the cable 210 includes a plug 200 having a pair of prongs 202 a and 202 b which are dimensioned to electrically and mechanically engage the electrosurgical energy generator. As explained in more detail below with respect to FIG. 8, the distal end of the cable 210 is secured to the proximal shaft connector 19 of shaft 12 b by a plurality of finger-like clamping members 77 a and 77 b and a cable crimp having opposing fingers 76 a and 76 b. The interior of cable 210 houses a pair of leads 210 a and 210 b which conduct the different electrical potentials from the electrosurgical generator to the jaw members 110 and 120 as explained in greater detail below.

As best seen in FIGS. 2-4B, the two opposing jaw members 110 and 120 of the end effector assembly 100 are pivotable about pin 150 from the open position to the closed position for grasping tissue 400 therebetween. Jaw members 110 and 120 are generally symmetrical and include similar component features which cooperate to permit facile rotation about pivot pin 150 to effect the grasping and sealing of tissue 400. As a result and unless otherwise noted, jaw member 110 and the operative features associated therewith will initially be described herein in detail and the similar component features with respect to jaw member 120 will be briefly summarized thereafter.

Jaw member 110 includes an insulated outer housing 114 which is dimensioned to mechanically engage an electrically conductive sealing surface 112 and a proximally extending flange 130 which is dimensioned to seat a distal connector 300 which is described in more detail below with respect to FIGS. 4A, 4B and 5. Preferably, outer insulative housing 114 extends along the entire length of jaw member 110 to reduce alternate or stray current paths during sealing and/or incidental burning of tissue 400. The inner facing surface of flange 130 includes an electrically conductive plate 134 (FIG. 4B) which conducts electrosurgical energy to the electrically conductive sealing surface 112 upon activation.

Likewise, jaw member 120 include similar elements which include: an outer housing 124 which engages an electrically conductive sealing surface 122; a proximally extending flange 140 which seats the opposite face of the distal connector 300; an electrically conductive plate 144 which conducts electrosurgical energy to the electrically conductive sealing surface 122 upon activation.

It is envisioned that one of the jaw members, e.g., 110, includes at least one stop member 150 disposed on the inner facing surface of the electrically conductive sealing surface 112 (and/or 122). Alternatively or in addition, the stop member 150 may be positioned adjacent to the electrically conductive sealing surfaces 112, 122 or proximate the pivot pin 151. The stop member(s) is preferably designed to facilitate gripping and manipulation of tissue 400 and to define a gap “G” (FIG. 6) between opposing jaw members 110 and 120 during sealing. Preferably the separation distance during sealing or the gap distance “G” is within the range of about 0.001 inches (˜0.03 millimeters) to about 0.006 inches (˜0.016 millimeters).

A detailed discussion of these and other envisioned stop members 150 as well as various manufacturing and assembling processes for attaching, disposing, depositing and/or affixing the stop members 150 to the electrically conductive sealing surfaces 112, 122 are described in commonly-assigned, co-pending PCT Application Serial No. PCT/US01/11222 entitled “BIPOLAR ELECTROSURGICAL FORCEPS WITH NON-CONDUCTIVE STOP MEMBERS” which is hereby incorporated by reference in its entirety herein. For the purposes of this disclosure at least the following text from PCT/US01/11222 is included herein. Corresponding reference numeral to the present disclosure are enclosed between parentheses“( ) ” for the purposes of clarity. In addition, FIGS. 2, 4, 15B and 16A-16G from the above disclosure are incorporated herein and renumbered as FIGS. 2′, 4′, 5′ and 6A′-6G′ for the purposes of clarity. The reference numerals associated with these figures also include a prime “′” designation for the purposes of clarity, e.g., 80′, 82′, etc.

As mentioned above, two mechanical factors play an important role in determining the resulting thickness of the sealed tissue and effectiveness of the seal, i.e., the pressure applied between opposing jaw members 80′ and 82′ (110 and 120) and the gap between the opposing jaw members 80′ and 82′ (110 and 120) during the sealing process. However, thickness of the resulting tissue seal cannot be adequately controlled by force alone. In other words, too much force and the two jaw members 80′ and 82′ (110 and 120) would touch and possibly short resulting in little energy traveling through the tissue thus resulting in a bad seal. Too little force and the seal would be too thick.

Applying the correct force is also important for other reasons: to oppose the walls of the vessel; to reduce the tissue impedance to a low enough value that allows enough current through the tissue; and to overcome the forces of expansion during tissue heating in addition to contributing towards creating the required end tissue thickness which is an indication of a good seal.

Preferably, the seal surfaces or tissue contacting surfaces 151′, 251′ (112, 122) (See renumber FIGS. 5′ and 6A′-6G′) of the jaw members 80′ and 82′ (110 and 120) are relatively flat to avoid current concentrations at sharp edges and to avoid arcing between high points. In addition and due to the reaction force of the tissue 150 when engaged, jaw members 80′ and 82′ (110 and 120) are preferably manufactured to resist bending. For example and as best seen in FIGS. 2′ and 6A′-6G′, the jaw members 80′ and 82′ (110 and 120) are preferably tapered along width “W” which is advantageous for two reasons: 1) the taper will apply constant pressure for a constant tissue thickness at parallel; 2) the thicker proximal portion of the jaw members 80′ and 82′ (110 and 120) will resist bending due to the reaction force of the tissue 150.

As best seen in FIG. 4′, in order to achieve a desired gap range (e.g., about 0.001 to about 0.005 inches and preferably about 0.002 inches to about 0.003 inches) and apply a desired force to seal the tissue, at least one jaw member 80′ and/or 82′ (110 and 120) includes a stop member 139′ (150) which limits the movement of the two opposing jaw members 80′ and 82′ (110 and 120) relative to one another. Preferably, stop member 139′ (150) extends from the sealing surface or tissue contacting surface 151′ (112 or 122) a predetermined distance according to the specific material properties (e.g., compressive strength, thermal expansion, etc.) to yield a consistent and accurate gap distance during sealing.

As explained above, in some cases it may be preferable to dimension stake 119′ such that it acts like a stop member and/or an additional stop member and also controls/limits the movement of the two opposing jaw members 80′ and 82′ (110 and 120) relative to one another. Preferably, stop member 139′ (150) and/or stake 119′ is made from an insulative material, e.g., parylene, nylon and/or ceramic and is dimensioned to limit opposing movement of the jaw members 80′ and 82′ (110 and 120) to within the above gap range.

FIG. 4A shows an exploded view of the various components of the forceps 10 and the inter-operative relationships among the same. More particularly and in addition to the components described above with respect to FIGS. 1-3 above, shaft 12 a is preferably hollow to define a longitudinal channel 15 a disposed therethrough which is dimensioned to receive a tube 60 a therein. Tube 60 a includes a proximal end 64 a, a distal end 62 a and at least one mechanical interface 61 a disposed therebetween. Shaft 12 a also includes a cover plate 50 which is designed for snap-fit engagement within an aperture/cavity 45 a defined through the outer surface of shaft 12 a. Cover plate 50 includes a series of opposing flanges 51 a and 51 b which extend therefrom which are dimensioned to secure the tube 60 a within shaft 12 a as described below. A second flange 52 secures the cover plate 50 to the shaft 12 a.

During assembly, the proximal end 64 a of tube 60 a is slideable incorporated within channel 15 a such that mechanical interface 61 a is poised for engagement with cover plate 50. Cover plate 50 is then snapped into cavity 45 a such that flanges 51 a and 51 b secure tube 60 a within shaft 12 a. It is envisioned that the cavity 45 a of shaft 12 a may include at least one detent (not shown) which engages mechanical interface 61 a disposed along the outer surface of tube 60 a to limit/prevent rotation of the tube 60 a relative to the shaft 12 a. This cooperative relationship is shown by way of example with respect to detents 75 a and 75 b and interfaces (e.g., notches) 61 b of shaft 12 b in FIG. 8. In this instance, flanges 51 a and 51 b (much like flanges 42 a and 42 b of cover plate 40 in FIG. 8) hold the detents 75 a and 75 b in FIG. 8) in secure engagement within the notch(es) 61 a to prevent rotational and/or longitudinal movement of the tube 60 a within the channel 15 a.

Preferably, the proximal-most end of tube 60 a includes a slit-like interface 65 a which mechanically engages a corresponding tongue 88 a extending from the inner surface of shaft 12 a within cavity 45 a. It is envisioned that tongue 88 a also prevents rotational movement of the tube 60 a within the shaft 12 a. Alternatively, slit 65 a may be formed to allow radial contraction and expansion of the tube 60 a to promote friction-fit engagement between the tube 60 a and the shaft 12 a. Other interfaces are also envisioned which will facilitate engagement of the shaft 12 a and the tube 60 a, e.g., snap-fit, spring-lock, locking tabs, screw-like interface, tongue and groove, etc.

The distal end 62 a of tube 60 a is preferably dimensioned to engage jaw member 120, i.e., the distal end 62 a includes a slit-like interface 66 a which promotes simple, secure friction-fit engagement of the tube 60 a with the jaw member 120. More particularly and as mentioned above, jaw member 120 includes a proximally extending flange 130 having a sleeve 128 extending proximally therefrom which is dimensioned such that, upon insertion of the sleeve 128 within distal end 62 a, slit-like interface 66 a expands radially outwardly and securely locks the jaw member 120 to tube 60 a. Again, other methods of attachment are also envisioned which would serve the same purpose, e.g., snap-locks, locking tabs, spring-locks, screw-like interface, tongue and groove, etc.

As can be appreciated by the present disclosure, the arrangement of shaft 12 b is slightly different from shaft 12 a as shown best in FIGS. 4B, 7 and 8. More particularly, shaft 12 b is also hollow to define a channel 15 b therethrough and is dimensioned to receive a tube 60 b therein. Tube 60 b includes a proximal end 64 b and a distal end 62 b which attach in a generally similar fashion as their counterpart components with respect to shaft 12 a. For example, the proximal end 64 b of tube 60 b is slideable incorporated within channel 15 b such that a mechanical interface 61 b disposed on the outer surface of tube 60 b is poised for engagement with a cover plate 40 (FIGS. 4A and 8).

Preferably and since the forceps 10 is uniquely designed to incorporate all of the electrical interfaces and connections within and along a single shaft, e.g., 12 b, shaft 12 b includes a slightly larger cavity 45 b defined therein for housing and securing the various electrical connections associated with the forceps 10 as described below. For example, cover plate 40 is dimensioned slightly differently than cover plate 50 mostly due to the spatial considerations which must be taken into account for incorporation of the various internally disposed electrical connections. However, cover plate 40 does snap atop shaft 12 b such that a pair of flanges 42 a and 42 b secure tube 60b within shaft 12 b in a similar manner as described above. For example, FIG. 8 shows a pair of detents 75 a and 75 b disposed within the cavity 45 b of shaft 12 b which engage a corresponding number of mechanical interfaces 61 b disposed along the outer surface of tube 60 b to limit/prevent rotation of the tube 60 b relative to the shaft 12 b. When assembled, each flange 42 a and 42 b is pushed into a corresponding groove 73 a and 73 b, respectively, which effectively maintain/hold the detents 75 a and 75 b in secure engagement within the notches 61 b to prevent rotational and/or longitudinal movement of the tube 60 b within the channel 15 b.

End 64 b of tube 60 b also includes a slit-like interface 65 b which mechanically engages a corresponding tongue 88 b extending from the inner surface of shaft 12 b within cavity 45 b. It is envisioned that tongue 88 a also prevents rotational movement of the tube 60 b within the shaft 12 b. Alternatively, slit 65 b may be formed to allow radial contraction and expansion of the tube 60 b to promote friction-fit engagement between the tube 60 b and the shaft 12 b.

Unlike tube 60 a, tube 60 b is designed as an electrical conduit for transmitting electrosurgical energy to jaw member 110 which is explained in more detail below with respect to FIGS. 7 and 8. The distal end 62 b of tube 60 b is preferably dimensioned to engage jaw member 110, i.e., the distal end 62 b includes a slit-like interface 66 b which promotes simple, secure friction-fit engagement of the tube 60 b with the jaw member 110. This is best illustrated in FIG. 4B which shows proximally extending flange 130 of jaw member 110 having a terminal sleeve 138 which extends therefrom. Terminal sleeve 138 is dimensioned such that, upon insertion of the terminal sleeve 138 within distal end 62 b, slit-like interface 66 b expands radially outwardly and securely locks the jaw member 110 to tube 60 b.

As can be appreciated, terminal end 138 is at least partially made from an electrically conductive material such that an electrosurgical potential is effectively conducted from the tube 60 b, through the terminal sleeve 138, across plate 134 and to the electrically conductive sealing plate 112 upon activation. As mentioned above, the outer insulative housing 114 of jaw member 110 effectively eliminates stray electrical currents and incidental burning of tissue across the intended electrical path.

As best shown in FIG. 4B, jaw member 110 includes a raceway 135 extending proximally from the flange 130 which includes terminal sleeve 138 at the proximal-most end thereof. The terminal sleeve 138 connects to the conductive tube 60b disposed within shaft 12 b as described above. Raceway 135 serves two purposes: 1) to provide electrical continuity from the terminal sleeve 138, through the electrically conductive plate 134 and to the electrically conductive sealing surface 112; and 2) to provide a channel for guiding lead 210 a to the distal connector 300 as described below.

Insulated outer housing 114 is dimensioned to securely engage the electrically conductive sealing surface 112. It is envisioned that this may be accomplished by stamping, by overmolding, by overmolding a stamped electrically conductive sealing plate and/or by overmolding a metal injection molded seal plate. All of these manufacturing techniques produce an electrode having an electrically conductive surface 112 which is substantially surrounded by an insulated outer housing 114.

It is envisioned that the jaw member may also include a second insulator (not shown) disposed between the electrically conductive sealing surface 112 and the outer insulative housing 114. The insulated outer housing 114 and the electrically conductive sealing surface 112 (and the other insulator if utilized) are preferably dimensioned to limit and/or reduce many of the known undesirable effects related to tissue sealing, e.g., flashover, thermal spread and stray current dissipation.

It is also envisioned that the electrically conductive sealing surface 112 may include a pinch trim (not shown) which facilitates secure engagement of the electrically conductive surface 112 to the insulated outer housing 114 and also simplifies the overall manufacturing process. It is also contemplated that the electrically conductive sealing surface 112 may include an outer peripheral edge which has a radius and the insulated outer housing 114 meets the electrically conductive sealing surface 112 along an adjoining edge which is generally tangential to the radius and/or meets along the radius. Preferably, at the interface, the electrically conductive surface 112 is raised relative to the insulated outer housing 114. These and other envisioned embodiments are discussed in concurrently-filed, co-pending, commonly assigned Application Serial No. PCT/US01/11412 entitled “ELECTROSURGICAL INSTRUMENT WHICH REDUCES COLLATERAL DAMAGE TO ADJACENT TISSUE” by Johnson et al. and concurrently-filed, co-pending, commonly assigned Application Serial No. PCT/US01/11411 entitled “ELECTROSURGICAL INSTRUMENT WHICH IS DESIGNED TO REDUCE THE INCIDENCE OF FLASHOVER” by Johnson et al.

As best illustrated in the exploded view of FIG. 4B, the inner periphery of tube 60 b is preferably dimensioned to house lead 210 a therethrough such that a different electrically potential can be effectively transmitted to jaw member 120. More particularly and as mentioned above, cable 210 houses two leads 210 a and 210 b having different electrical potentials. The first lead 210 a is disposed through tube 60 b and conducts the first electrical potential to jaw member 120 as described in more detail below. The second lead 210 b is electrically interfaced with tube 60 b at a proximal connector 80 (FIG. 7) which includes a series of electrical crimps 85, 87 and 89 for securing lead 210 b to tube 60 b. As a result, tube 60 b carries the second electrical potential therethrough for ultimate connection to jaw member 110 as described above.

Lead 210 a preferably includes an insulative coating 213 which surrounds an inner core or electrical conductor 211 (e.g., wire) disposed therein to insulate the electrical conductor 211 from the tube 60 b during activation. It is envisioned that the wire 211 may be made from a solid or multi-strand electrically conductive material, e.g., copper/aluminum, which is surrounded by an insulative, non-conductive coating 213 , e.g., plastic.

The wire 211 includes a terminal end 212 which is dimensioned to electrically interface with jaw member 120. Preferably, the terminal end 212 is “flat-formed” in a generally arcuate shape to encircle a corresponding boss 314 which extends upwardly from the distal connector 300 towards jaw member 120 as described below. It is envisioned that the distal connector 300 performs at least two functions: 1) to insulate jaw member 110 from jaw member 120; and 2) to provide a running electrical connection for lead 210 a to jaw member 120.

More particularly, the distal connector 300 is generally shaped to match the overall profile of the electrically conductive face plates 134 and 144 of jaw members 110 and 120, respectively, such that, upon assembly, outer facing surfaces 302 and 304 of the distal connector 300 abut against the corresponding plates 134 and 144 of jaw member 110 and 120, respectively. It is envisioned that the outer facing surface 302 of the distal connector 300 acts as a runway surface which facilitates pivotable motion of jaw member 120 about pivot pin 151 relative to jaw member 110. Preferably, the distal connector 300 is made form an insulative substrate such as plastic or some other non-conductive material.

The distal connector includes a series of flanges 322 and 326 which extend towards jaw member 120 and a second series of flanges 324 and 328 which extend towards jaw member 110. It is envisioned that these flanges 322, 324, 326 and 328 insulate the other operative components of the forceps 10 and the patient from stray electrical currents emanating from the electrically conductive plates 134 and 144 during activation. Flanges 322 and 328 may also be dimensioned to limit/restrict the expansion of tissue 400 beyond the sealing surfaces 112 and 122 during activation. Flanges 326 and 324 are preferably dimensioned to insulate the forceps during all angles of operation, i.e., pivoting of the jaw members 110 and 120.

As mentioned above, the distal connector 300 includes a boss 314 which extends towards jaw member 120 which is dimensioned to secure the terminal end 212 of lead 210 a. Preferably, the boss is designed to electrically insulate the terminal end of the lead from the pivot. The boss 314 preferably defines an aperture 316 therethrough for receiving the pivot pin 151 and to allow pivotable motion of jaw member 120 about the pivot 151 and the boss 314 relative to jaw member 110.

A continuous series of recesses 312, 318 and 319 are formed around and proximate boss 314 to seat the flat-formed terminal end 212, the wire 211 and the insulated portion of the lead 210 a, respectively. This also secures lead 210 a to the distal connector and limits movement of the same (210 a). In some cases it may be preferable to include a dollop of silicone or other non-conductive material at the junction between the wire and the terminal end 212 as an added and/or alternative insulating safeguard. It is also envisioned that flange 326 may include a notch (not shown) disposed therethrough which facilitates assembly of the lead 210 a atop the distal connector 300. As can be appreciated, this eliminates the step of forming the arcuately-shaped terminal end 212 after insertion through channel 318. As mentioned above, a dollop of silicone or the like may be added atop/within the notch for insulation purposes after the terminal end 212 is seated within the distal connector 300.

The proximal-most portion of distal connector 300 includes a finger 320 which is dimensioned to seat within a channel 137 formed within the raceway 135 such that the distal connector 300 moves in connection with jaw member 110 during pivoting. Channel 135 may be formed during a molding process, subsequently bored after the raceway 135 is formed or by any other known method of formation. The uppermost edge of boss 314 is preferably dimensioned to seat within a corresponding recess (not shown) formed within plate 144. Likewise and although not shown, it is envisioned that the opposite end of boss 314 extends towards plate 134 and seats within a recess 131 formed within plate 134. It is envisioned that recess 131 promotes engagement of the distal connector 300 with the jaw member 110.

The distal connector 300 also includes a spring washer or wave washer 155 which is preferably dimensioned to encircle the boss 314 atop terminal end 212. Upon assembly, the washer 212 is sandwiched/wedged between the terminal end 212 and the conductive plate 144 of jaw member 120. It is envisioned that the washer 155 enhances the connection between the terminal end and the plate 144. More particularly, the washer 155 is preferably shaped such that the washer 155 provides a self-cleaning, running electrical contact between the terminal end 212 and the jaw member 120. It is contemplated that the washer 155 “self-cleans” due to the frictional contact and relative movement of the washer 155 with respect to the terminal end 212 during pivoting of the jaw members 110 and 120. The self-cleaning action can be attributed to the washer 155 rubbing, scoring and/or digging against the terminal end 212 and/or the plate 144 during pivoting of the jaw members 110 and 120.

The outer housing of each of the jaw members 110 and 120 preferably includes an additional recess or circular groove 129 which receives a ring-like insulator 153 b and 153 a, respectively. Insulators 153 a and 153 b insulate the pivot pin 150 from the jaw members 110 and 120 when the forceps 10 is assembled. Preferably, the pivot pin 150 is peened to secure the jaw members 110 and 120 during assembly and may include outer rims 151 a and 151 b at least one of which is peened or formed after the jaw members 110 and 120 are assembled about the pivot pin 150 as best shown in FIG. 4B.

Upon activation, the first electrical potential is carried by lead 210 a through tube 60 b to the terminal end 212. The washer 155 of the distal connector 300 then conducts the first potential to face plate 144 which carries the first potential to sealing plate 122 disposed on the inner facing surface of jaw member 120. The second potential is carried by lead 210 b which electrically interfaces with the tube 60 b (by way of crimps 85, 87 and 89) to conduct the second potential to terminal sleeve 138 of jaw member 110. The terminal sleeve 138 electrically connects to sealing surface 112 across face plate 134.

FIG. 8 shows the connection of the cable 210 within the cavity 45 b of shaft 12 b. As mentioned above a series of finger-like elements 77 a and 77 b and crimps 76 a and 76 b secure the cable 210 within shaft 12 b. Preferably, cable 210 is secured at an angle alpha (α) relative to a longitudinal axis “A” disposed along shaft 12 b. It is envisioned that angling the cable 210 in an inward direction, i.e., towards shaft 12 a, facilitates handling of the forceps 10 and the cable 210 during surgery, i.e., the angled disposition of the cable 210 as it exits the forceps 10 tends to reduce cable tangling and/or cable interference during handling.

Preferably at least one of the jaw members 110 and 120 includes a skirt-like feature 126 and 136, respectively, which is dimensioned to prevent exposure of the terminal end 212 or wire 211 during all angles of operation, i.e., when the jaw members 110 and 120 are disposed in the first open position, the second closed position and/or during operative movement therebetween.

It is envisioned that by making the forceps 10 disposable, the forceps 10 is less likely to become damaged since it is only intended for a single use and, therefore, does not require cleaning or sterilization. As a result, the functionality and consistency of the vital sealing components, e.g., the conductive surfaces 112 and 122, the stop member(s) 150, and the insulative housings 124 and 114 will assure a uniform and quality seal.

From the foregoing and with reference to the various figure drawings, those skilled in the art will appreciate that certain modifications can also be made to the present disclosure without departing from the scope of the present disclosure. For example, it may be preferable to include a tang which facilitates manipulation of the forceps 10 during surgery.

Moreover, although the electrical connections are preferably incorporated with the bottom shaft 12 b and the instrument is intended for right-handed use, it is contemplated the electrical connections may be incorporated with the other shaft 12 a depending upon a particular purpose and/or to facilitate manipulation by a left-handed user.

It is also contemplated that a shrink tube may be employed over the proximal connector 80 and/or the other various solder or crimp connections 85, 87 and 89 associated with the proximal connector 80 interface with lead wire 210 b. This provides additional insulating protection during assembly. An insulative sheath may also be used to cover the end effector assembly 100 or the outer surfaces (non-opposing surfaces) of the jaw members 110 and 120.

It is also contemplated that the forceps 10 (and/or the electrosurgical generator used in connection with the forceps 10) may include a sensor or feedback mechanism (not shown) which automatically selects the appropriate amount of electrosurgical energy to effectively seal the particularly-sized tissue 400 grasped between the jaw members 110 and 120. The sensor or feedback mechanism may also measure the impedance across the tissue during sealing and provide an indicator (visual and/or audible) that an effective seal has been created between the jaw members 110 and 120.

Experimental results in animal studies suggest that the magnitude of pressure exerted on the tissue by the seal surfaces 112 and 122 is important in assuring a proper surgical outcome. Tissue pressures within a working range of about 3 kg/cm² to about 16 kg/cm² and, preferably, within a working range of 7 kg/cm² to 13 kg/cm² have been shown to be effective for sealing arteries and vascular bundles. Tissue pressures within the range of about 4 kg/cm² to about 6.5 kg/cm² have proven to be particularly effective in sealing arteries and tissue bundles.

In one embodiment, the shaft portions are manufactured such that the spring constant of the shaft portions 12 a and 12 b, in conjunction with the placement of the ratchet interfaces 32 a and 32 b, will yield pressures within the above working range. In addition, the successive positions of the ratchet interfaces increase the pressure between opposing seal surfaces 112 and 122 incrementally within the above working range.

It is envisioned that the outer surface of the jaw members 110 and 112 may include a nickel-based material, coating, stamping, metal injection molding which is designed to reduce adhesion between the jaw members 110, 112 (or components thereof) with the surrounding tissue during activation and sealing. Moreover, it is also contemplated that other components such as the shaft portions 12 a, 12 b and the ring holes 18 a, 18 b may also be coated with the same or a different “non-stick” material. Preferably, the non-stick materials are of a class of materials that provide a smooth surface to prevent mechanical tooth adhesions.

It is also contemplated that the tissue sealing surfaces 112 and 122 of the jaw members 110 and 120 can be made from or coated with these non-stick materials. When utilized on the sealing surfaces 112 and 122, these materials provide an optimal surface energy for eliminating sticking due in part to surface texture and susceptibility to surface breakdown due electrical effects and corrosion in the presence of biologic tissues. It is envisioned that these materials exhibit superior non-stick qualities over stainless steel and should be utilized on the forceps 10 in areas where the exposure to pressure and electrosurgical energy can create localized “hot spots” more susceptible to tissue adhesion. As can be appreciated, reducing the amount that the tissue “sticks” during sealing improves the overall efficacy of the instrument.

The non-stick materials may be manufactured from one (or a combination of one or more) of the following “non-stick” materials: nickel-chrome, chromium nitride, MedCoat 2000 manufactured by The Electrolizing Corporation of OHIO, Inconel 600 and tin-nickel. For example, high nickel chrome alloys and Ni200, Ni201 (˜100% Ni) may be made into electrodes or sealing surfaces by metal injection molding, stamping, machining or any like process.

The Inconel 600 coating is a so-called “super alloy” which is manufactured by Special Metals, Inc. located in Conroe Tex. The alloy is primarily used in environments which require resistance to corrosion and heat. The high Nickel content of Inconel makes the material especially resistant to organic corrosion. As can be appreciated, these properties are desirable for bipolar electrosurgical instruments which are naturally exposed to high temperatures, high RF energy and organic matter. Moreover, the resistivity of Inconel is typically higher than the base electrode material which further enhances desiccation and seal quality.

As mentioned above, the tissue sealing surfaces 112 and 122 may also be “coated” with one or more of the above materials to achieve the same result, i.e., a “non-stick surface”, For example, Nitride coatings (or one or more of the other above-identified materials) may be deposited as a coating on another base material (metal or nonmetal) using a vapor deposition manufacturing technique.

One particular class of materials disclosed herein has demonstrated superior non-stick properties and, in some instances, superior seal quality. For example, nitride coatings which include, but not are not limited to: TiN, ZrN, TiAlN, and CrN are preferred materials used for non-stick purposes. CrN has been found to be particularly useful for non-stick purposes due to its overall surface properties and optimal performance. Other classes of materials have also been found to reducing overall sticking. For example, high nickel/chrome alloys with a Ni/Cr ratio of approximately 5:1 have been found to significantly reduce sticking in bipolar instrumentation. One particularly useful non-stick material in this class is Inconel 600. Bipolar instrumentation having sealing surfaces 112 and 122 made from or coated with Ni200, Ni201 (˜100% Ni) also showed improved non-stick performance over typical bipolar stainless steel electrodes.

While several embodiments of the disclosure have been shown in the drawings, it is not intended that the disclosure be limited thereto, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplications of preferred embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto. 

1. A bipolar electrosurgical instrument for use in open surgery, comprising: first and second shafts each having a jaw member extending from a distal end thereof and a handle disposed at a proximal end thereof for effecting movement of the jaw members relative to one another from a first position wherein the jaw members are disposed in opposable, spaced relation relative to one another to a second position wherein the jaw members cooperate to grasp tissue therebetween, each of the jaw members including an electrically conductive sealing surface; a source of electrical energy having first and second electrical potentials, the first electrical potential being connected to one of the jaw members and a second electrical potential being connected to the other of the jaw members such that the jaw members are capable of selectively conducting energy through tissue held therebetween to effect a seal, wherein the first electrical potential is transmitted through the first shaft by a lead having a terminal end which electrically interfaces with distal connector which connects one of the jaw members to the first electrical potential; and at least one non-conductive stop member disposed on the electrically conductive sealing surface of at least one of the jaw members which controls the distance between the electrically conductive sealing surfaces when tissue is held therebetween.
 2. A bipolar electrosurgical instrument for use in open surgery according to claim 1 wherein the at least one non-conductive stop creates a gap between the electrically conductive sealing surfaces within the range of about 0.001 inches to about 0.006 inches.
 3. A bipolar electrosurgical instrument for use in open surgery according to claim 1 wherein the non-conductive stop creates a gap between the electrically conductive sealing surfaces within the range of about 0.002 inches to about 0.003 inches.
 4. A bipolar electrosurgical instrument for use in open surgery, comprising: first and second shafts each having a jaw member extending from a distal end thereof and a handle disposed at a proximal end thereof for effecting movement of the jaw members relative to one another from a first position wherein the jaw members are disposed in opposable, spaced relation relative to one another to a second position wherein the jaw members cooperate to grasp tissue therebetween, each of the jaw members including an electrically conductive sealing surface; a source of electrical energy having first and second electrical potentials, the first electrical potential being connected to one of the jaw members and a second electrical potential being connected to the other of the jaw members such that the jaw members are capable of selectively conducting energy through tissue held therebetween to effect a seal, wherein the first electrical potential is transmitted through the first shaft by a lead having a terminal end which electrically interfaces with a distal connector which connects one of the jaw members to the first electrical potential; at least one non-conductive stop member disposed on the electrically conductive sealing surface of at least one of the jaw members which controls the distance between the electrically conductive sealing surfaces when tissue is held therebetween; and a ratchet disposed on the first shaft and at least one complimentary interlocking mechanical interface disposed on the second shaft, the ratchet and the complimentary interlocking mechanical interface providing at least one interlocking position to maintain a closure pressure in the range of about 3 kg/cm² to about 16 kg/cm² between the electrically conductive sealing surfaces.
 5. A bipolar electrosurgical instrument according to claim 4 wherein the ratchet and the complimentary interlocking mechanical interface provide at least one interlocking position to maintain a closure pressure in the range of about 7 kg/cm² to about 13 kg/cm² between the electrically conductive sealing surfaces.
 6. A bipolar electrosurgical instrument according to claim 4 further comprising a non-stick material disposed on the electrically conductive sealing surfaces.
 7. A bipolar electrosurgical instrument according to claim 4 wherein the non-conductive stop member is disposed adjacent the electrically conductive sealing surfaces.
 8. A bipolar electrosurgical instrument according to claim 6 wherein the non-stick material is a coating which is deposited on the electrically conductive sealing surfaces.
 9. A bipolar electrosurgical instrument according to claim 8 wherein the non-stick coating is selected from a group of materials consisting of: nitrides and nickel/chrome alloys.
 10. A bipolar electrosurgical instrument according to claim 8 wherein the non-stick coating includes one of TiN, ZrN, TiAIN, CrN, nickel/chrome alloys with a Ni/Cr ratio of approximately 5:1, Inconel 600, Ni200 and Ni201.
 11. A bipolar electrosurgical instrument according to claim 6 wherein the electrically conductive sealing surfaces are manufactured from a non-stick material.
 12. A bipolar electrosurgical instrument for use in open surgery, comprising: first and second shafts each having a jaw member extending from a distal end thereof and a handle disposed at a proximal end thereof for effecting movement of the jaw members relative to one another from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members cooperate to grasp tissue therebetween, each of the jaw members including an electrically conductive sealing surface; a source of electrical energy having a first electrical potential connected to one of the jaw members and a second electrical potential connected to the other of the jaw members such that the jaw members are capable of selectively conducting energy through tissue held therebetween to effect a seal; the first and second electrical potentials being transmitted to the jaw members through the first shaft wherein the first electrical potential is transmitted by a lead having a terminal end which electrically interfaces with a spring washer, the spring washer acting as an electrical intermediary between the terminal end and the jaw member; at least one non-conductive stop member disposed on the electrically conductive sealing surface of at least one of the jaw members which controls the distance between the jaw members when tissue is held therebetween, wherein the at least one non-conductive stop creates a gap between the electrically conductive surfaces within the range of about 0.001 inches to about 0.006 inches; and a ratchet disposed on the first shaft and at least one complimentary interlocking mechanical interface disposed on the second shaft, the ratchet and the complimentary interlocking mechanical interface providing at least one interlocking position to maintain a closure pressure in the range of about 3 kg/cm² to about 16 kg/cm² between the electrically conductive sealing surfaces. 